EP4006579A1 - Method and system for compensating depth-dependent attenuation in ultrasonic signal data - Google Patents

Method and system for compensating depth-dependent attenuation in ultrasonic signal data Download PDF

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Publication number
EP4006579A1
EP4006579A1 EP20315466.1A EP20315466A EP4006579A1 EP 4006579 A1 EP4006579 A1 EP 4006579A1 EP 20315466 A EP20315466 A EP 20315466A EP 4006579 A1 EP4006579 A1 EP 4006579A1
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EP
European Patent Office
Prior art keywords
data
depth
different depths
attenuation
medium
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EP20315466.1A
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German (de)
English (en)
French (fr)
Inventor
Christophe Fraschini
Bo Zhang
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SuperSonic Imagine SA
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SuperSonic Imagine SA
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Priority to EP20315466.1A priority Critical patent/EP4006579A1/en
Priority to AU2021232671A priority patent/AU2021232671B2/en
Priority to JP2021149455A priority patent/JP7250870B2/ja
Priority to KR1020210122471A priority patent/KR102606973B1/ko
Priority to US17/474,650 priority patent/US20220163646A1/en
Priority to CN202111275311.5A priority patent/CN114601498A/zh
Publication of EP4006579A1 publication Critical patent/EP4006579A1/en
Pending legal-status Critical Current

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Definitions

  • the present invention relates to imaging methods and apparatus implementing said methods, in particular for medical imaging.
  • the present disclosure concerns a method for compensating a depth-dependent attenuation in ultrasonic (i.e. ultrasound) signal data of a medium.
  • the method may be implemented by a processing system which is for example associated to a plurality (e.g. a line or an array) of transducers in relation with said medium.
  • Classical ultrasound imaging consists of an insonification of a medium with one or several ultrasound pulses (or waves) which are transmitted by a transducer. In response to the echoes of these pulses ultrasound signal data are acquired, as example by using the same transducer.
  • a complete line of the image can be computed using a dynamic receive beamforming process.
  • this procedure is repeated by sending a set of focused waves that scan along a lateral line at given depth (named the focal plane).
  • a dynamic beamforming is performed, and the complete image is obtained, built line by line.
  • the dynamic beamforming guarantees a uniform focusing in the receive mode, whereas, in the transmit mode the focus is fixed at a given depth.
  • the final image is optimal in the focal plane and in a limited region of the medium corresponding to the focal axial length. However, outside this area, which is imposed by diffraction laws, the image quality is rapidly degraded at other depths (in the near and far fields of the focused beam).
  • a solution is to perform multi-focus imaging: different transmit focal depths are used to obtain a homogeneous quality all over the image.
  • Each transmission at a given focal depth enables performing a partial image in the region delimited by the axial focal length.
  • the final image is obtained using a recombination of these partial images envisioned by performing synthetic dynamic transmit focalization.
  • Such approach consists in re-synthesizing a dynamic transmit focusing (i.e. as many focal depths as pixel in the image) by beamforming and then combining a set of different insonifications.
  • a B-mode image (Brightness) can be prepared, which displays the acoustic impedance of a two-dimensional cross-section of the imaged medium.
  • ultrasound attenuation within an examined medium.
  • tissue(s) As ultrasound propagates in tissue(s), it is subjected to an attenuation effect as a function of depth and of tissue properties. This results in spectral deformation of the received signal at different depths.
  • Attenuation thereby constitutes a subtle frequency and depth dependent phenomenon. It is thus desirable to compensate any effects of attenuation on the resulting computed image, as it is conventionally done by for example time-gain compensation to account for tissue attenuation.
  • US5879303A describes an ultrasonic diagnostic imaging method which produces ultrasonic images from harmonic echo components of a transmitted fundamental frequency.
  • a proposed attenuation compensation consists in blending fundamental and harmonic signals.
  • different frequency-response filters are proposed as a function of depth.
  • the known methods are either unprecise, as they for example disregard nonlinearity of the attenuation, or they are complex, as they for example mandatorily require a plurality of different filters for compensating the attenuation effect.
  • the method and system desirably provide improved image quality, for example in terms of speckle/clutter reduction, and/or of increased sharpness.
  • a method for compensating a depth-dependent attenuation in ultrasonic signal data of a medium is provided.
  • Said method is implemented by a processing system, for example associated to at least one ultrasound transducer (which may be put in relation with said medium).
  • the method comprises the following steps:
  • the attenuation compensation step may lead to a spectrum shifting across the different depths of the medium which compensates any shift caused by the attenuation effect.
  • the shifting amount and the bandwidth of the low pass filter may be estimated automatically as a function of depth.
  • the attenuation effect in the ultrasound signal data can be compensated (i.e. corrected) by respective signal data processing. Hence, no adaptation of any filters in depth applied to the processed signal data is required.
  • the present disclosure leads to better B-mode image quality in terms of noise reduction and of image sharpness.
  • the method of the present disclosure allows using a single conventional filter in a subsequent filtering step.
  • the method of the present disclosure achieves a depth-dependent spectrum shifting for compensating the attenuation effect, it is not necessary to adapt the filter or use several respectively adapted filters (e.g. non-centered filters) for different depth to match the unaligned spectrum of the input data. This advantageously simplifies the filter design.
  • the method and system of the present disclosure is general and is thus applicable to any attenuation and is not limited to linear attenuation.
  • the present disclosure thereby allows an improved image quality (e.g. of B-mode images) in terms of speckle/clutter reduction, and of sharpness and at the same time is a more computation-efficient approach than conventional techniques which uses specific filters for a depth-dependent attenuation correction.
  • the method of the present disclosure is computationally more efficient (i.e. requires less calculations).
  • Different depths may mean different depth levels (e.g. discrete values) or different depth areas (e.g. a range or interval between two neighboured depth levels).
  • the compensated IQ data spectrum may be re-centered at a predefined reference frequency, for example at zero frequency or another predefined positive or negative value.
  • the method of the present disclosure may comprise the further step after the processing step and before the attenuation compensation step: a shift amount determination step in which for each of the plurality of different depths a frequency shift amount is determined based on a predefined shift map.
  • the shift map may also be predetermined as a function of one or several different ultrasound transducer types and/or one or several different medium types.
  • the map may comprise one or several different coefficients for each transducer type and/or for each medium type.
  • the shift map may be derived from a single predefined attenuation coefficient or multiple attenuation coefficients respectively for the plurality of different depths.
  • said attenuation coefficient may specify a decrease of ultrasound amplitude in the ultrasonic signal data as a function of frequency per unit of distance in the depth direction of the medium (dB/cm/MHz).
  • the map may comprise only one attenuation coefficient, based on which a linear shift function may be determined.
  • said coefficient may define the gradient of the linear function.
  • the shift map comprises a plurality of coefficients, for example each one for a respective depth range in the medium.
  • the respectively obtained linear functions may be combined.
  • the method of the present disclosure may comprise the further steps after the processing step and before the attenuation compensation step:
  • the shift amount is not necessarily based on predetermined data (e.g. a predefined shift map or a table) but it may also be determined automatically by the method of the present disclosure.
  • Said auto-correlation function may be for example an order 1 auto-correlation function.
  • the attenuation compensation step may be done in the time domain by multiplication of a complex phase for each of the plurality of different depths on the input data processed by the attenuation compensation step up to a maximum depth z max .
  • the complex phase at a depth z k may for example be a function of the total shift amount up to the depth z k .
  • the maximum depth z max may be the maximum depth in the ultrasound data. Accordingly, the data may be corrected at each depth up to a predefined maximum depth z max . Only this maximum depth z max is desirably (pre)defined by the probe or the system or the user.
  • the data at a depth z 1 , z 2 , z n may be multiplied each by a phase computed up to z 1 , z 2 , z n .
  • z 1 , z 2 , z n may be discrete depth data between 0 and Zmax.
  • said maximum depth may correspond to a value selected by a user or may be predefined by the system representing a maximum depth of the region in the medium scanned in a ultrasound imaging method.
  • the depth may be any kind of predefined or preselected value.
  • the method of the present disclosure is computationally advantageously much more efficient than doing the compensation in the spectral domain.
  • the method may further comprise the steps after the processing step:
  • the bandwidth of the spectrum may be adapted to compensate any effects of the bandwidth on the ultrasound signal data.
  • the ultrasonic signal data usually comprises data of a plurality of ultrasound lines of at least one ultrasound transducer.
  • the center estimation step and/or the bandwidth estimation step may then be performed for each of the plurality of ultrasound lines.
  • the output data of said steps may be smoothed (for example, averaged) across the ultrasound lines optionally additionally as a function of predefined rules and parameters.
  • the data obtained by the center estimation step and/or the bandwidth estimation step for each line may be combined to smooth the combined data, for example by determining an average between the data for each line.
  • the accuracy of the attenuation compensation and/or the bandwidth correction may be enhanced.
  • the output data may optionally be smoothed across the ultrasound lines as a function of further predefined rules and parameters, for example the number of ultrasound lines of the used transducer, and/or the transducer type, and/or the medium.
  • the output data of the center estimation step and/or the bandwidth estimation step may be regularized by a regularization step in depth direction.
  • the robustness of the output data of the center estimation step and/or the bandwidth estimation step may be enhanced by hypothesis-testing a pure noise model. Only statistically significant points may be included in the output data such that the output data are less biased by noise.
  • 0 where ⁇ 1 stands for order-1 autocorrelation coefficient may be tested.
  • may be derived such that the probability of observing
  • This step in particular the hypothesis-testing step, may be done prior to the center estimation step and/or the bandwidth estimation step, for example also prior to the processing step of the present disclosure and may provide predetermined data used in center estimation step and/or the bandwidth estimation step.
  • any combination of the above-mentioned steps, in particular the steps for smoothing the combined output data between lines, for regularizing the output data and for enhancing the robustness of the output data may be combined.
  • a frequency shift map across the depth may be generated based on the frequency shift amounts for the different depths by fitting piecewise attenuation functions, for example linear or non-linear functions, for adjacent depths (i.e. depth ranges or regions in the depth direction) to the map.
  • the method of the present disclosure may desirably be part of a scattering or backscattering process, in particular a beamforming process method, for instance a synthetic beamforming process.
  • the in-phase and quadrature phase (IQ) data may be scattered and/or backscattered IQ data, in particular they may be beamformed IQ data.
  • the method of the present disclosure comprises a beamforming step in which the IQ data is processed by a beamforming process for providing beamformed acquisition data of the medium.
  • the processing step, the attenuation compensation step and any steps between these steps may be performed in the beamforming process.
  • the beamforming process may be for example a synthetic beamforming process. This advantageously allows to further reduce the diffraction pattern.
  • the processing of the ultrasound data in the method of the present disclosure may be done in the processing steps of the beamforming process that comprises IQ data rephasing. Accordingly, the method of the present disclosure does not imply any significant additional computational costs.
  • the method may be implemented by a processing system associated or linked to at least one ultrasound transducer.
  • the method may comprise the further steps before the processing step:
  • the method may further comprise at least one of the steps:
  • the filtering step may comprise using a single lowpass filter and/or a bandpass filter. It may also comprise using a plurality of lowpass filter and/or a bandpass filter. Desirably only one filter may be used which is applied to a plurality of different depths, as the input signal data inputted into the filter have already a recentered spectrum (i.e. the attenuation has already been compensated by the spectrum shift in the input signal data). It is though also possible to use several filters. for example, having different bandwidths for each depth level.
  • only one filter e.g. a lowpass or bandpass filter
  • the filter may be predefined, or may be selected from a predefined list as a function of transducer and/or medium, or may be adaptable when the method is carried out (e.g. the filter can be determined to have the average bandwidth of those estimated by the method).
  • the used filter may though be adapted for a depth-dependent bandwidth adaptation, as described above.
  • Each filter may have an adapted, possibly different bandwidth(s).
  • the centers of the filters may be aligned. Accordingly, the filters do not necessarily have different central frequencies, as said spectral shift is already achieved in the attenuation compensation step.
  • the present disclosure further relates to a computer program comprising computer-readable instructions which when executed by a data processing system cause the data processing system to carry out the method for compensating depth-dependent attenuation in ultrasonic signal data of a medium as described above.
  • the present disclosure further may further relate to a method for imaging an ultrasound image, wherein in the image processing the attenuation effect has been compensated as described above.
  • the image(s) may then be displayed on any associated display, local or remote, during the same or similar time period and/or location or not.
  • the present disclosure further relates to a system for compensating a depth-dependent attenuation in ultrasonic signal data of a medium, comprising a processing system configured to:
  • the system may optionally also comprise an ultrasound data acquisition system, for example comprising at least one transducer.
  • an ultrasound data acquisition system for example comprising at least one transducer.
  • the system of the present is not limited to this option.
  • the system may be configured to receive ultrasound signal data from an external acquisition system which is for instance connectable to the system of the present disclosure via the internet, the 'cloud', 4G or 5G protocols, WIFI, any local network or any other data contact or contactless connection.
  • the at least one transducer may be a single transducer configured to transmit a pulse and receive the tissue response.
  • a focalized transducer having for example a concave form or a respective lens. It is additionally possible to sweep the single transducer.
  • a linear array may be provided typically including a few tens of transducers (for instance 100 to 300) juxtaposed along an axis X (horizontal or array direction X).
  • 3D probes or any other probe may also be used for implementation of the present disclosure.
  • the same transducer(s) may be used to transmit a pulse and receive the response, or different transducers are used for transmission and reception.
  • the present disclosure may further relate to a computer program including instructions for executing the steps of at least one of the methods described above, when said program is executed by a computer.
  • the present disclosure may also relate to a recording medium readable by a computer and having recorded thereon a computer program including instructions for executing the steps of at least one of the methods described above, when said program is executed by a computer.
  • the disclosure and it's embodiments may be used in the context of medical devices dedicated to human beings, animals, but also any material to be considered such as metallic pieces, gravel, pebbles, etc..
  • the apparatus shown on Fig. 1 is adapted for imaging of a region 1 of a medium, for instance living tissues and in particular human tissues of a patient or an animal or a plant.
  • the apparatus may correspond to the system of the present disclosure.
  • the apparatus may include for instance:
  • the transducer is external to the electronic bay 3 and/or the microcomputer 4.
  • the transducer may be remotely connectable to the electronic bay 3 and/or the microcomputer 4.
  • the transducer is an IOT device and/or is connectable to an IOT device and/or to a smartphone.
  • the transducer may be connectable to the electronic bay 3 and/or the microcomputer 4 via the internet, the 'cloud', 4G or 5G protocols, WIFI, any local network or any other data contact or remote connection.
  • the electronic bay 3 and the microcomputer 4 are remotely connectable, for example via the internet, the 'cloud', 4G or 5G protocols, WIFI, any local network or any other data contact or remote connection.
  • the apparatus may further comprise a display for showing ultrasound images.
  • Said display may be connected to or be comprised by the microcomputer 4. It is also possible that display is remotely connectable to the electronic bay 3 and/or the microcomputer 4, for example via the internet, the 'cloud', 4G or 5G protocols, WIFI, any local network or any other data contact or remote connection.
  • the axis Z on figure 1 is an axis perpendicular to the axis X, and it is usually the direction of ultrasound beams generated by the transducers of the array, for example in the depth direction of the examined medium. This direction is designated in present document as a vertical or axial direction.
  • the electronic bay 3 may include for instance:
  • the apparatus herein disclosed is a device for ultrasound imaging, the transducers are ultrasound transducers, and the implemented method estimates an ultrasonic attenuation parameter for region 1 and optionally may produce ultrasound images of region 1.
  • the apparatus may be any imaging device using other waves than ultrasound waves (waves having a wavelength different than an ultrasound wavelength), the transducers and the electronic bay components being then adapted to said waves.
  • Fig. 3 shows a flowchart of a method for compensating a depth-dependent attenuation in ultrasonic signal data of a medium according the present disclosure. Said method may be implemented in the apparatus of Fig. 1 .
  • the method steps may be controlled mainly by a processing system 8, for example comprising the central processing unit 8a and/or the GPU 8b, eventually with the contribution of the digital signal processor 10, or any other means.
  • the method includes the following main steps:
  • the method may further comprise an optional beamforming step (c-f) comprising the processing step (c), the attenuation compensation step (f) and any steps between (c) and (f), wherein in the optional beamforming step the IQ data is processed by a beamforming process for providing beamformed acquisition data of the medium.
  • the method may be carried out repeatedly, for example by a loop from step (h) back to step (a). In this way a repeated ultrasound data acquisition and /or ultrasound imaging becomes possible, for example in real-time or quasi real-time.
  • Fig. 4 shows a diagram of a first exemplary embodiment (using a predefined coefficient / map) of the method according to the present disclosure.
  • the method may comprise an optional shift amount determination step (d1) in which for each of the plurality of different depths (z 1 , z 2 , z n ) a frequency shift amount is determined based on a predefined shift map, for example also as a function of the probe type.
  • a predefined shift map for example an attenuation coefficient, may be obtained to compute the amount of frequency shift as a function of depth.
  • the frequency shifts are applied on the input IQ data.
  • the correction may be done in the time domain by the multiplication of a complex phase on the input data that corresponds to the shift amount.
  • the corrected data are then low pass filtered to reduce noise, before being sent to envelop detection.
  • Fig. 5 shows a diagram of a second exemplary embodiment (using automated shift amount determination) of the method according the present disclosure.
  • the method may comprise an optional function determination step (d2) in which for each of a plurality of different depths (z 1 , z 2 , z n ) in the medium an auto-correlation function of the IQ data is determined.
  • the method may comprise a subsequent optional center estimation step (e2) in which for each of the plurality of different depths (z 1 , z 2 , z n ) a central spectral location ⁇ c ( z) is estimated as a function of a phase of the auto-correlation function.
  • the attenuation compensation step (f) for each different depth (z 1 , z 2 , z n ) the frequency shift amount is determined as a function of the respective central spectral location ⁇ c (z).
  • the frequency shift may be automatically estimated by an order-1 autocorrelation on the IQ data.
  • the order-1 autocorrelation function R 1 (z) and coefficient ⁇ 1 (z) may be computed from the IQ at each depth.
  • the central spectral location ⁇ c (z) at each depth z is estimated by the phase of R 1 : ⁇ c z ⁇ ⁇ R 1 z
  • the IQ data phase at each depth may be compensated (corrected) by using this estimated location, such that the corrected data spectrum is re-centered at zero frequency.
  • Fig. 6 shows a diagram of a third exemplary embodiment (additionally using automated bandwidth correction) of the method according the present disclosure.
  • the method may further comprise an optional bandwidth estimation step (e2') in which for each of the plurality of different depths (z 1 , z 2 , z n ) a respective spectral standard deviation is estimated as a function of an autocorrelation coefficient of the IQ data.
  • the method may comprise further a subsequent an optional bandwidth determination step (f2") in which for each of the plurality of different depths (z 1 , z 2 , z n ) a frequency bandwidth of a filter is determined as a function of the spectral standard deviation, such that the IQ data is adaptively filtered across the plurality of different depths.
  • a filtering step (g) may be carried out where the filter is applied to the compensated IQ data.
  • the spectral standard deviation may be estimated at each depth z by: ⁇ ⁇ z ⁇ 2 1 ⁇ ⁇ 1 z
  • Both estimates may be further improved in accuracy by smoothing the estimates from multiple ultrasound lines. Both estimates may also be regularized in depth to have smoother variation as a function of depth, and thus to improve the stability of the filtering.
  • the robustness of both estimators may be improved by hypothesis-testing a pure noise model i.e. H 0 :
  • 0. Only statistically significant points are included in the estimation such that the estimates are less biased by noise.
  • Fig. 7a shows a first example of a depth-dependent spectrum of an ultrasound image without attenuation compensation.
  • Fig. 7b shows the same first example with attenuation compensation, an example of automatic spectrum correction as a function of depth on a phantom with a linear attenuation coefficient.
  • the ultrasound signal spectrum is distorted by attenuation when propagating in depth.
  • the method according to the present disclosure allows to automatically estimate the frequency center and the bandwidth at each depth. This allows to recenter the spectrum, and adaptively low-pass filter the ultrasound signal data, to compensate the attenuation distortion.
  • the method is applicable to nonlinear attenuation also.
  • fig. 7b it is exemplarily and schematically shown that a single lowpass filter may be used for each depth level in the spectrum. This is possible, because a depth-dependent spectrum shifting for attenuation compensation has already been carried out by the method of the present disclosure.
  • Fig. 8a shows a second example of a depth-dependent spectrum of an ultrasound image without attenuation compensation, wherein fig. 8b shows another example with attenuation compensation.
  • the attenuation is not necessarily linear.
  • Said example illustrates an in vivo example and the result of the automatic correction as disclosed.
  • fig. 8b it is exemplarily and schematically shown that a plurality of filters of matching bandwidths may be used for a respective plurality of depth levels in the spectrum.
  • a plurality of filters of matching bandwidths may be used for a respective plurality of depth levels in the spectrum.
  • Said filters may be lowpass filters. They may be identical with regard to their center. In other words, the filters may not need to match any spectrum shifting of the ultrasound signal data.
  • the filters may though differ with regard to their bandwidth.
  • the filters may have varying bandwidths across the depth. Accordingly it becomes possible to use filters of different matching bandwidths across different depths. Said bandwidths may be calculated for example in steps d2' and e2' as described above.
  • the method according the present disclosure allows a more precise attenuation estimation and implies less computational costs, what in particular improves a real time computation mode. Further, due to the increased preciseness a decreased variance and thus an increased reproducibility can be achieved.

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EP20315466.1A 2020-11-25 2020-11-25 Method and system for compensating depth-dependent attenuation in ultrasonic signal data Pending EP4006579A1 (en)

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EP20315466.1A EP4006579A1 (en) 2020-11-25 2020-11-25 Method and system for compensating depth-dependent attenuation in ultrasonic signal data
AU2021232671A AU2021232671B2 (en) 2020-11-25 2021-09-14 Method and system for compensating depth-dependent attenuation in ultrasonic signal data
JP2021149455A JP7250870B2 (ja) 2020-11-25 2021-09-14 超音波信号データにおける深度依存性の減衰を補償するための方法及びシステム
KR1020210122471A KR102606973B1 (ko) 2020-11-25 2021-09-14 초음파 신호 데이터의 깊이 의존 감쇠를 보상하는 방법 및 시스템
US17/474,650 US20220163646A1 (en) 2020-11-25 2021-09-14 Method and system for compsensating depth-dependent attenuation in ultrasonic signal data
CN202111275311.5A CN114601498A (zh) 2020-11-25 2021-10-29 用于超声信号数据中与深度有关的衰减的补偿方法和系统

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Citations (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5879303A (en) 1996-09-27 1999-03-09 Atl Ultrasound Ultrasonic diagnostic imaging of response frequency differing from transmit frequency
US20170105705A1 (en) * 2014-03-26 2017-04-20 Samsung Electronics Co., Ltd. Adaptive demodulation method and apparatus for ultrasound image

Family Cites Families (11)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CA1135827A (en) * 1978-12-04 1982-11-16 Rainer Fehr Determination of flow velocities by measuring phase difference between the doppler signals
US4534220A (en) * 1984-01-27 1985-08-13 Kleeper John R Apparatus for measuring the characteristics of an ultrasonic wave medium
AU3361095A (en) * 1994-08-05 1996-03-04 Acuson Corporation Method and apparatus for transmit beamformer system
US5935074A (en) * 1997-10-06 1999-08-10 General Electric Company Method and apparatus for automatic tracing of Doppler time-velocity waveform envelope
US7837624B1 (en) * 1998-11-20 2010-11-23 Siemens Medical Solutions Usa, Inc. Medical diagnostic ultrasound imaging methods for extended field of view
US7887487B2 (en) * 2005-07-11 2011-02-15 Siemens Medical Solutions Usa, Inc. Ultrasound diagnostic flow imaging with coded excitation
JP5511201B2 (ja) * 2008-07-31 2014-06-04 キヤノン株式会社 信号処理装置、超音波装置、信号処理装置の制御方法及び超音波装置の制御方法
KR102389866B1 (ko) * 2014-12-30 2022-04-22 삼성전자주식회사 초음파 영상을 생성하는 방법 및 영상 처리 장치
US20200225347A1 (en) * 2015-12-09 2020-07-16 University Of Rochester Fine-tuning the h-scan for visualizing types of tissue scatterers
KR102022144B1 (ko) * 2015-12-24 2019-09-17 지멘스 메디컬 솔루션즈 유에스에이, 인크. 신호의 감쇠를 적응적으로 보상하는 초음파 시스템 및 방법
CN114129172A (zh) * 2016-05-03 2022-03-04 阿库图森医疗有限公司 具有效率算法的心脏标测系统

Patent Citations (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5879303A (en) 1996-09-27 1999-03-09 Atl Ultrasound Ultrasonic diagnostic imaging of response frequency differing from transmit frequency
US20170105705A1 (en) * 2014-03-26 2017-04-20 Samsung Electronics Co., Ltd. Adaptive demodulation method and apparatus for ultrasound image

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